EP0562862B1 - Matériaux bioabsorbables pour implants cicatrisants - Google Patents

Matériaux bioabsorbables pour implants cicatrisants Download PDF

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Publication number
EP0562862B1
EP0562862B1 EP93302316A EP93302316A EP0562862B1 EP 0562862 B1 EP0562862 B1 EP 0562862B1 EP 93302316 A EP93302316 A EP 93302316A EP 93302316 A EP93302316 A EP 93302316A EP 0562862 B1 EP0562862 B1 EP 0562862B1
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EP
European Patent Office
Prior art keywords
substructure
sponge
bioabsorbable
oriented
heteromorphic
Prior art date
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Expired - Lifetime
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EP93302316A
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German (de)
English (en)
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EP0562862A1 (fr
Inventor
Arthur L. Rosenthal
Nicholas D. Light
Paul W. Watt
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Ethicon Inc
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Johnson and Johnson Medical Inc
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/58—Materials at least partially resorbable by the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F13/00987—Apparatus or processes for manufacturing non-adhesive dressings or bandages
    • A61F13/00991—Apparatus or processes for manufacturing non-adhesive dressings or bandages for treating webs, e.g. for moisturising, coating, impregnating or applying powder
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F13/15—Absorbent pads, e.g. sanitary towels, swabs or tampons for external or internal application to the body; Supporting or fastening means therefor; Tampon applicators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
    • A61L15/225—Mixtures of macromolecular compounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties
    • A61L15/425—Porous materials, e.g. foams or sponges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties
    • A61L15/54—Radio-opaque materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties
    • A61L15/64—Use of materials characterised by their function or physical properties specially adapted to be resorbable inside the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/54—Biologically active materials, e.g. therapeutic substances
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/56—Porous materials, e.g. foams or sponges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F2013/00089—Wound bandages
    • A61F2013/00093—Wound bandages tubular
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F2013/00089—Wound bandages
    • A61F2013/00217—Wound bandages not adhering to the wound
    • A61F2013/00221—Wound bandages not adhering to the wound biodegradable, non-irritating
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F2013/00089—Wound bandages
    • A61F2013/00246—Wound bandages in a special way pervious to air or vapours
    • A61F2013/00255—Wound bandages in a special way pervious to air or vapours with pores
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F2013/00361—Plasters
    • A61F2013/00855—Plasters pervious to air or vapours
    • A61F2013/00863—Plasters pervious to air or vapours with pores
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
    • A61F2310/00005—The prosthesis being constructed from a particular material
    • A61F2310/00365—Proteins; Polypeptides; Degradation products thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/412—Tissue-regenerating or healing or proliferative agents

Definitions

  • the present invention relates to bioabsorbable wound implant materials, and more particularly to heteromorphic sponge materials containing an oriented substructure, which are suitable for use as implantable materials in wound repair.
  • Porous materials formed from synthetic and/or naturally occurring bioabsorbable materials have been used in the past as wound dressings or implants.
  • the porous material provides structural support and a framework for tissue ingrowth while wound healing progresses.
  • the porous material is gradually absorbed as the tissue around the wound regenerates.
  • Typical bioabsorbable materials for use in the fabrication of porous wound dressings or implants include synthetic bioabsorbable polymers such as polylactic acid or polyglycolic acid, and also biopolymers such as the structural proteins and polysaccharides.
  • the structural proteins include collagen, elastin, fibronectin, laminin and fibrin, as well as other proteins of the human connective tissue matrix. Of these, the most studied material has been collagen.
  • Collagen is the most abundant animal protein and the major protein of skin and connective tissue. A high degree of homology exists between the various types of collagen found in different animal species and human collagen. Accordingly, animal collagen types such as bovine collagen are useful because they exhibit very low immunogenicity when implanted into humans or used as topical dressings on human wounds.
  • Collagen may be prepared in a variety of physical forms including fibres, flakes, films or aqueous gels. Freeze drying an aqueous gel or an aqueous suspension of collagen may be used to produce a porous collagen sponge.
  • Collagen sponges are described, for example, in Chvapil, J. Biomed. Mater. Res. 11 721-741 (1977). The use of collagen sponges and/or other freeze-dried biopolymer sponges as wound dressings or implant materials is disclosed, for example, in US-A-4614794 and US-A-4320201.
  • High molecular weight polysaccharides of the mammalian connective tissue matrix have also been used in various types of wound dressing or "synthetic skins". Yannas I.V. & Burke, J.F., J. Biomed. Mater. Res. 14 56-81 (1980) describe the use of such polysaccharides in wound dressings formed by freeze drying as sponges.
  • High molecular weight polysaccharides include such molecules as chondroitin sulphate, hyaluronic acid and dermatan sulphate.
  • US-A-4614794 describes the use of other naturally occurring polysaccharide materials, especially of plant origin, in the dressing of wounds. These include, for example, alginates, chitosan, chitin, guar gum, and various plant gums.
  • Porous materials comprising more than one kind of bioabsorbable polymer have also been suggested for use as wound implants or wound dressings.
  • bioabsorbable polymer having more than one kind of bioabsorbable polymer
  • GB-A-2215209 (Osmed Inc.) describes a biodegradable, osteogenic bone-graft substitute comprising: (a) a porous, rigid structure formed from a biodegradable polymer such as polylactic or polyglycolic acid; (b) a chemotactic substance such as hyaluronic acid, fibronectin or collagen dispersed in the interstices of the rigid structure, and (c) a biologically active or therapeutic substance such as bone morphogenetic protein.
  • the material is implanted into a bone defect. The material helps to restore functional architecture and mechanical integrity of the bone, initiate osteogenesis, and maintain the biological processes of bone growth while simultaneously being slowly bioabsorbed by the host organism.
  • JP-A-03023864 (Gunze KK) describes a reinforced collagen sponge for use as a filling material for biological tissue.
  • the collagen sponge is reinforced by the addition of fibres of poly-(L-lactic acid).
  • the resulting fibre-reinforced composite sponge is stronger than pure collagen or cross-linked collagen sponges, and is bioabsorbed more slowly in a host organism.
  • EP-A-0274898 describes surgical implant materials based on open-cell sponges of bioabsorbable polyesters such as polylactide/polyglycolide.
  • One or more bioabsorbable textile reinforcing elements e.g. parallel fibres or threads or net-like flat structures, are embedded in the open-cell sponge to provided mechanical reinforcement.
  • wound implants comprising a matrix of bioabsorbable sponge and a bundle of hollow bioabsorbable filaments extending through the sponge for draining wound fluid out of the wound cavity and for injecting therapeutic substances into the wound cavity.
  • Implants made from biological, bioabsorbable components are normally intended to be invaded by the cells of the host or recipient of the implant.
  • Cellular invasion of homogeneous sponge implants is not necessarily achieved in the most efficient manner.
  • the closed honeycomb nature of sponges presents a series of "walls" to cells invading the structure, each of which has to be breached before progress can continue.
  • Cellular invasion is required by cells which can degrade the implant materials and by those which can lay down the tissue to replace the implant and thus repair any defect which the implant is intended to repair. Failure of either type of cell to invade the structure of the implant in an efficient manner prevents vascularisation which is required for new tissue to be able to sustain its life.
  • porous bioabsorbable implants that have been suggested to date are generally isotropic materials. That is to say, the structure and composition of the materials are generally uniform in all directions. This does not conform to the reality of wound healing, according to which vascularisation and tissue ingrowth into wounds are highly directional. For example, tissue ingrowth normally takes place from the edges of a skin wound, and not from the wound bed.
  • the implant material should be anisotropic so as to allow rapid tissue ingrowth in the preferred wound healing direction while maintaining maximum structural stability in all other directions.
  • the present invention provides a bioabsorbable heteromorphic sponge comprising a matrix structure of sponge and at least one oriented substructure embedded therein, wherein the matrix and the substructure are formed of bioabsorbable materials, and characterised in that the substructure comprises films, or flaked or broken films, that are sufficiently oriented to provide for anisotropic cellular ingrowth into the sponge.
  • the present invention also provides a bioabsorbable heteromorphic sponge comprising a matrix structure of sponge and at least one oriented substructure embedded therein, wherein the matrix and the substructure ate formed of bioabsorbable materials, characterised in that said substructure defines linear channels for anisotropic cellular ingrowth into the sponge, and provided that the substructure does not comprise hollow filaments for the passage of liquids through the sponge.
  • the present invention also provided a method of preparing such sponges as defined is claim 7.
  • the term “heteromorphic” means that the sponges according to the present invention are structurally inhomogeneous due to the presence of the substructure in the sponge matrix.
  • the sponges according to the present invention may also be chemically inhomogeneous if the substructure has a different chemical composition than the sponge matrix.
  • the substructure in the heteromorphic sponge according to the present invention is oriented. That is to say, the substructure is anisotropic and thereby defines preferred directions for cellular ingrowth into the sponge.
  • the sponge is bioabsorbable in that it is capable of full degradation and resorption within a patient's body.
  • the heteromorphic sponge is preferably used as a wound implant for example in partial or full thickness skin injury or in tissue insufficiency where soft tissues are required to be replaced.
  • the matrix and the substructure are both formed from biodegradable biopolymer materials.
  • the matrix is preferably strong and resilient enough to resist collapse and may be cut and/or formed so as to conform to a wound shape so that it protects and/or fills a wound bed. It may, for example, be cut so as to fill the full depth of a wound or tissue deficient area.
  • a heteromorphic sponge which has been cut to shape can then be placed into a debrided wound bed.
  • a wound which has a heteromorphic sponge implanted therein may then be dressed with a suitable dressing and healing allowed to take place. Regrowth of new tissue into the heteromorphic sponge enhances wound healing.
  • the heteromorphic sponge may allow wound fluid, oxygen and other gases to pass through the sponge and can be replaced by host tissues in such a way that healing is promoted and cosmetic damage minimised.
  • the sponge matrix comprises one or more proteins or one or more polysaccharides, or a mixture of one or more proteins with one or more polysaccharides.
  • the sponge matrix consists essentially of collagen.
  • the collagen may be provided by harvesting it as a fibrous mass containing largely collagen types I and III from such animal sources as skin, tendon, intra-organ connective tissue and bone and from such species as cattle, sheep, pigs, chickens, turkeys, kangaroo, deer or other mammals.
  • the sponge matrix and substructures within the matrix may include all collagen types, tenascin, laminin, chondroitin sulphate, hyaluronic acid, dermatan sulphate, heparin sulphate, heparin, elastin, fibrin, fibronectin, vitronectin, dextran, or oxidised regenerated cellulose.
  • the substructures are non-randomly deposited, oriented substructures. They may be formed from material which is the same material as that of the matrix or may be formed from another material.
  • the substructure may be films, flaked or otherwise broken films, fibres, fibre bundles or mixtures of these.
  • the substructures may comprise materials which make up for tissue deficiency or which contain active agents which may control, enhance or encourage wound healing.
  • the oriented substructures within the matrix provide conduits or pathways for cells to follow, enabling them to invade into the body of the matrix of the heteromorphic sponge.
  • the substructures are elongate or flat and planar, such as films or film flakes, fibres or fibre bundles.
  • the sponge component of the matrix thus has its homogeneous structure sufficiently interrupted by the substructures to facilitate cellular movement.
  • endothelial cells and fibroblasts can migrate relatively rapidly in the matrix structure and begin, at an early stage after implantation, the process of degradation and renewal.
  • At least 75% of the substructure is oriented within 30 degrees of a mean direction of orientation of the substructure.
  • the substructure comprises fibres or fibre bundles, preferably at least 75% of the fibres are oriented within 30 degrees of the mean direction of orientation of the fibres.
  • the substructure comprises flakes or films or other substantially planar fragments, coplanarity of the planar fragments is not required provided that the fragments of the substructure are sufficiently oriented to provide for anisotropic cellular ingrowth into the heteromorphic sponge.
  • the planar fragments could be organised like the cell walls of a honeycomb, defining one-dimensional channels for cellular ingrowth.
  • planar fragments of the substructure are arranged in a substantially coplanar stack such that the heteromorphic sponge has a laminated structure.
  • This arrangement provides two-dimensional planes for cellular ingrowth.
  • at least 75% of the planar fragments are oriented such that their perpendiculars are inclined at an angle of 30 degrees or less to the mean perpendicular direction.
  • At least 75% of the substructure is oriented within 20 degrees of a mean direction of orientation of the substructure.
  • the heteromorphic sponge may further include materials which are active in aiding in the healing process.
  • Active molecules may include: antimicrobials to control infection; cytokines and growth factors to enhance healing; antibodies to specific wound components such as TGFß to prevent contracture; collagen; peptides to act as chemotactic agents, angiogenic factors, hormones and enzymes; or pain killers.
  • the heteromorphic sponge may be formed by making a heterogeneous premix comprising the substructure material suspended in a gel, paste, slurry or emulsion of the matrix material which is then freeze dried.
  • the orientation of the substructure may be achieved in different ways.
  • the elements of the substructure such as films, fibres and the like may be laid down in an ordered fashion in a bath of the matrix gel, paste or slurry.
  • the substructure may be an ordered structure such as a honeycomb of the substructure material which is then flooded with the matrix gel, paste or slurry.
  • Spontaneous ordering of the substructure can also take place. For example, where flakes of the substructure material are stirred into a slurry as above and the mixture is allowed to stand before freeze drying, spontaneous ordering of the flakes is observed in the freeze-dried product. Spontaneous ordering of flakes and fibres also occurs when pastes or gels containing these substructures are extruded.
  • fibrous collagen pre-washed to remove the majority of non-collagenous components as described in US-A-4614794 or US-A-4320201 is suspended in clean deionised pyrogen free water and homogenised to a fine fibrous suspension by passage through a homogenising system. Suitable homogenising systems are described in US-A-4320201.
  • Homogenisation may be continued until a desired degree of fibre division is achieved. This results in a preferred fibre size of between 0.01 and 10 mm.
  • homogenised collagen is acidified to cause it to swell to a premix or gel suitable for freeze drying.
  • the acidifying step may use an organic acid such as formic, acetic, propionic, lactic, malonic, or dilute inorganic acids such as hydrochloric acid at a solids content of between 0.01% and 30% to a final pH of between 2 and 6.
  • a preferred embodiment results in a pH of between 3.0 and 4.5.
  • Adding sub-components to the matrix which enhance the regrowth of tissues preferably produces a final concentration of between 0.01% and 50% of the dry weight of the material.
  • the second components may then be mixed so as to disperse them throughout the body of the premix.
  • Mixing usually comprises stirring and may further include adding cross-linking agents to stabilise the matrix.
  • a plasticiser such as glycerol or sorbitol may be added to a final concentration of between 0.1% and 5%, based on the dry weight of collagen, and mixed with the premix. Oil may also be added at this stage with adequate homogenisation.
  • the resulting matrix may comprise a slurry, gel, paste, emulsion or suspension which may then be mixed quickly with a preformed, fabricated solid material of the substructure to form the heterogeneous mix desired. This is then preferably fully degassed, poured into trays and freeze dried.
  • the heteromorphic sponge can be freeze dried at its desired final thickness or dried as a block and cut to size and shape prior to packaging and sterilisation. Where a film is produced, this may be rolled onto tube carriers or pre-cut into lengths and stored flat. Films may also be made by pouring a slurry of collagen onto flat trays and drying in a stream of warm air at between 20°C and 80°C.
  • Drugs or active agents which are required for incorporation into the heteromorphic sponges may be added to the sponge mixture or to the second components which will become substructures of the sponge before these are added to the premix for freeze drying.
  • An isomorphic single-component collagen sponge is prepared as follows.
  • An acetic acid suspension of collagen is prepared substantially as described above and in US-A-4614794.
  • the suspension is adjusted to 0.45% solids, degassed and poured into trays to a depth of 3mm.
  • the mixture is rapidly frozen and freeze dried.
  • the resultant material is an isomorphic, substantially homogeneous collagen sponge.
  • a two-component heteromorphic sponge containing oriented film laminae is prepared as follows:
  • a gel or slurry of fibrous collagen is prepared as described above.
  • Glycerol is added as a plasticiser to a final weight of 0.5% and the gel is then extruded through a suitable flat bed, slit extruder onto a moving belt of suitable material so as to form a fine, unbroken film on the conveyor.
  • the moving conveyor belt passes through a drying cabinet with the temperature set at 55°C.
  • the dry film is stored by rolling onto tube carriers or as pre-cut lengths stored flat in boxes.
  • the films are made by pouring the slurry of collagen onto flat trays and drying in a stream of warm air.
  • the two-component heteromorphic sponge system is made by fabricating pre-cast and dried films with sponge premix, as follows. A layer of collagen sponge gel or slurry is poured at a thickness of 1mm and blast frozen. Collagen film is then placed onto the frozen slurry and a second layer of collagen slurry poured to a required thickness. This composite is then blast frozen. Collagen slurry and film layers can be built up to any desired thickness by this procedure. It is also possible, but less convenient, to layer collagen film onto unfrozen collagen slurry followed by a second layer of unfrozen collagen slurry.
  • oxidised regenerated cellulose is obtained commercially in the form of SurgicelTM fabric and is pre-coated with hyaluronic acid (1% solution in water) and re-dried in warm air.
  • This material is used as the uppermost lamina in a sponge film laminated structure made as described above.
  • An advantage of this material is found to be that it can be sutured into place in the wound bed, the SurgicelTM providing strength to hold the sutures.
  • the degree of orientation of the substructure is determined by scanning electron microscopy (SEM) at 100x magnification of the sponge material sectioned at right angles to the plane of substructure orientation.
  • SEM scanning electron microscopy
  • the substructure films are found to be highly oriented, with a standard deviation from the plane of orientation (ten data points) of only 2 degrees.
  • a two-component heteromorphic sponge containing oriented flaked film fragments is prepared as follows. Flakes of the film described in Example 2 are made by homogenising dry collagen film in a Waring Blendor three times, each for 30 sec. at high speed. Larger film flakes are prepared by homogenising for shorter time periods. The flakes of film are then quickly dispersed in the collagen sponge gel (or slurry) described in Example 1 and the mixture is poured into trays and freeze dried.
  • the degree of orientation of the substructure flakes is determined by SEM as described above.
  • the flakes show roughly coplanar orientation with a standard deviation (based on measurements on 10 flakes) of 12 degrees.
  • the orientation of the flakes appears to have taken place spontaneously in the precursor slurry.
  • a two-component heteromorphic sponge containing a substructure of oriented fibres is prepared as follows.
  • a three-component heteromorphic sponge is made as follows. Collagen film flakes and fibres are incorporated together into a collagen sponge gel or slurry and heteromorphic sponges are made as described in Examples 3 and 4.
  • a heteromorphic sponge containing oriented substructure of collagen film is prepared as in Example 2.
  • Discs of this sponge of thickness 3mm and diameter 1cm are implanted subcutaneously via 1.5cm incisions through the paniculus carnosus of male Sprague Dawley rats (200-250g) and the incision closed by suture.
  • the rats are sacrificed after 3, 7 and 14 days and the implant and surrounding tissue removed for histological examination.
  • the examination shows that inflammatory cells (polymorphonuclear cells and macrophages), and subsequently fibroblasts, have infiltrated the sponge matrix of the implant by directed migration along the direction of the laminae of the substructure.

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Claims (8)

  1. Eponge hétéromorphe bioabsorbable comprenant une structure matricielle d'éponge et au moins une substructure orientée qui y est incluse, dans laquelle la matrice et la substructure sont formées de matériaux bioabsorbables et caractérisée en ce que la substructure comprend des films, ou des films floconnés ou cassés en morceaux qui sont suffisamment orientés pour offrir un développement cellulaire interne anisotrope dans ladite éponge.
  2. Eponge hétéromorphe bioabsorbable comprenant une structure matricielle d'éponge et au moins une substructure orientée qui y est incluse, dans laquelle la matrice et la substructure sont formées de matériaux bioabsorbables, caractérisée en ce que ladite substructure définit des canaux linéaires pour le développement cellulaire interne anisotrope dans ladite éponge, et étant entendu que ladite substructure ne comprend pas de filaments creux pour le passage des liquides à travers ladite éponge.
  3. Eponge hétéromorphe bioabsorbable selon la revendication 1 ou 2, dans laquelle les matériaux bioabsorbables sont identiques ou différents et comprennent des macromolécules biopolymères choisies dans le groupe comprenant tous les types de collagènes, l'élastine, la fibronectine, la laminine, la tenascine, l'acide hyaluronique, le sulfate de chrondroïtine, le sulfate de dermatane, la fibrine, le dextrane, le sulfate d'héparine, la vitronectine, la cellulose régénérée oxydée et leurs mélanges.
  4. Eponge hétéromorphe bioabsorbable selon la revendication 1, 2 ou 3 dans laquelle au moins 75 % de la substructure sont orientés à moins de 30 degrés d'une direction moyenne d'orientation de la substructure.
  5. Eponge hétéromorphe bioabsorbable selon la revendication 4, dans laquelle au moins 75 % de la substructure sont orientés à moins de 20 degrés d'une direction moyenne d'orientation de la substructure.
  6. Eponge hétéromorphe bioabsorbable selon l'une quelconque des revendications précédentes, qui comprend en outre au moins un matériau qui est actif pour favoriser la cicatrisation..
  7. Procédé de préparation d'une éponge hétéromorphe bioabsorbable selon l'une quelconque des revendications 1 à 6, comprenant une structure matricielle d'éponge et au moins une substructure orientée, ledit procédé comprenant les étapes qui consistent :
    à fournir un gel, une pâte, une suspension ou une émulsion d'un premier matériau bioabsorbable et d'un solvant ;
    à fournir une substructure solide orientée d'un second matériau bioabsorbable immergé dans le gel, la pâte, la suspension ou l'émulsion, où ladite substructure est suffisamment orientée pour offrir des conduits ou des passages pour le développement cellulaire interne anisotrope dans ladite éponge ; et
    à lyophiliser le gel, la pâte, la suspension ou l'émulsion pour produire l'éponge hétéromorphe bioabsorbable.
  8. Procédé selon la revendication 7, dans lequel ladite étape qui consiste à fournir une substructure solide orientée comprend l'extrusion du gel, de la pâte, de la suspension ou de l'émulsion dans lequel est immergé le second matériau bioabsorbable, pour orienter le second matériau bioabsorbable dans ladite substructure.
EP93302316A 1992-03-25 1993-03-25 Matériaux bioabsorbables pour implants cicatrisants Expired - Lifetime EP0562862B1 (fr)

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GB929206504A GB9206504D0 (en) 1992-03-25 1992-03-25 Heteromorphic sponges as wound implants

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DE69329211D1 (de) 2000-09-21
ATE195413T1 (de) 2000-09-15
CA2092344C (fr) 2005-06-14
GB9206504D0 (en) 1992-05-06
DE69329211T2 (de) 2001-04-05
EP0562862A1 (fr) 1993-09-29
US5700477A (en) 1997-12-23
CA2092344A1 (fr) 1993-09-26
BR9301313A (pt) 1993-09-28

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